JP2010051729A - Ultrasonic diagnostic device, ultrasonic image processing device and ultrasonic image processing program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic device, an ultrasonic image processing device and an ultrasonic image processing program removing noise generated originating in respiratory body motion when acquiring a plurality of two-dimensional ultrasonic images while rotating an ultrasonic scanning plane around a certain axis and reconstructing a three-dimensional image using these. <P>SOLUTION: When scanning a three-dimensional region while rotating the scanning plane around a predetermined axis (rotation axis), the ultrasonic diagnostic device calculates the motion vector of a motion scanning plane (ultrasonic sectional layer) using ultrasonic image data on the rotation axis, and corrects a positional mismatch between the scanning planes using this. Also, as needed, the motion vector is calculated and the positional mismatch between the sectional layers is corrected using at least one frame having a cardiac time phase close to the frame of which the motion should be corrected and being spatially close to the frame in addition to the frames with the same cardiac time phase as the frame of which the motion should be corrected. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention generates an image due to body movement due to respiration in an ultrasonic diagnostic apparatus that performs four-dimensional display (real-time three-dimensional display) using a multi-plane ultrasonic endoscope probe (MTEE probe) or the like. The present invention relates to a technique for removing noise.

  Ultrasound diagnosis can be performed repeatedly by simply touching the ultrasound probe from the body surface, and the heart beats and fetal movements can be obtained in real time, and it is highly safe. . In addition, it can be said that this is a simple diagnostic method in which the scale of the system is smaller than other diagnostic devices such as X-rays, CT, and MRI, and inspection can be easily performed while moving to the bedside. Ultrasound diagnostic devices used in this ultrasound diagnosis vary depending on the types of functions that they have, but small ones that can be carried with one hand have been developed. Thus, there is no influence of exposure, and it can be used in obstetrics and home medical care.

  In such an ultrasonic diagnostic apparatus, there is a technique for scanning a three-dimensional region using an MTEE probe, generating a three-dimensional image using the obtained data, and displaying it in real time. Here, the MTEE probe is used when a probe is inserted into a patient's esophagus to observe the heart, and a cross section at an arbitrary angle can be observed by rotating a one-dimensional array transducer. . If this MTEE probe is slowly rotated through 180 °, the entire 360 ° field of view is obtained. Therefore, when the MTEE probe is used, a three-dimensional image as a still image or a real-time three-dimensional image (four-dimensional image) can be constructed if the target is stationary. On the other hand, when the object is moving like a heart, a correct three-dimensional image or four-dimensional image cannot be constructed.

  By the way, as a technique for generating and displaying a four-dimensional image of an organ in which a target is moving periodically, such as a heart, there is one described in Patent Document 1, for example. In this method, a plurality of frames of a predetermined time phase are acquired and reconstructed while rotating or swinging the probe in synchronization with the patient's ECG signal. This makes it possible to display a three-dimensional image at a predetermined time phase as if the heart was stationary.

  While slowly rotating the MTEE probe at a constant speed, a two-dimensional image is continuously collected in association with an ECG signal, and a three-dimensional image is obtained using images of the same cardiac time phase among a plurality of collected two-dimensional images Images can also be reconstructed. By performing this operation for each cardiac time phase, it is possible to create a four-dimensional image that expresses how the heart is moving over one cardiac cycle. Also, a method for calculating a cardiac cycle from an image instead of an ECG signal has been proposed (see, for example, Patent Documents 2 and 3).

In addition, as a well-known document relevant to this application, there exist the following, for example.
US Pat. No. 5,159,941 JP 2005-74225 A US Pat. No. 6,966,878

  However, when the above method is applied to four-dimensional image generation / display using the MTEE probe, there are the following problems.

  That is, in the generation and display of a four-dimensional image using the MTEE probe, about 1080 two-dimensional images must be obtained in order to actually obtain a beautiful four-dimensional image. For this purpose, for example, when the heart rate is 60 beats / minute, the tomographic scan is 30 frames / second, and the rotational angle of the probe for each tomographic image is 0.167 °, a scanning time of 36 seconds is required. If the heart moves due to the patient's breathing during this period, the effect appears as distortion of the heart shape as shown in FIG. 15 on the four-dimensional image.

  This problem is caused by assuming that the heart wall and the valve are in the same three-dimensional position and shape in the same heartbeat time phase. This assumption is correct with some accuracy if there is no arrhythmia and there is no movement of the entire heart due to respiration. However, even if there is no arrhythmia, this assumption does not hold because the entire heart moves if the patient breathes. This method has a major problem because it is impossible to breathe for 36 seconds while the endoscope is swallowed.

  The present invention has been made in view of the above circumstances, and acquires a plurality of two-dimensional ultrasonic images while rotating an ultrasonic scanning surface around a certain axis, and reconstructs a three-dimensional image using them. In some cases, an object of the present invention is to provide an ultrasonic diagnostic apparatus, an ultrasonic image processing apparatus, and an ultrasonic image processing program that can remove noise generated due to respiratory motion.

  In order to achieve the above object, the present invention takes the following measures.

  According to the first aspect of the present invention, the diagnostic object is three-dimensionally ultrasonically scanned while rotating the scanning surface around the rotation axis, and ultrasonic image data of a plurality of frames corresponding to the plurality of scanning surfaces is acquired. Based on data corresponding to the rotational axis of the plurality of ultrasonic image data, correction means for correcting the positional deviation between the frames, and a plurality of frames in which the positional deviation has been corrected. An ultrasonic diagnostic apparatus comprising: image generation means for generating a three-dimensional image using ultrasonic image data.

  The invention according to claim 8 is an ultrasonic image of a plurality of frames corresponding to a plurality of scanning planes acquired by three-dimensionally ultrasonically scanning the diagnostic object while rotating the scanning plane about the rotation axis. And a storage means for storing data, and a correction means for correcting a positional deviation between the frames based on data corresponding to the rotation axis of the plurality of ultrasonic image data. This is a sonic diagnostic image processing apparatus.

  According to the ninth aspect of the present invention, a plurality of frames corresponding to a plurality of scanning planes obtained by three-dimensionally ultrasonically scanning a diagnostic object while rotating the scanning plane about a rotation axis is used. Among the ultrasonic image data, based on data corresponding to the rotation axis, using a correction function for correcting the positional deviation between the frames, and the ultrasonic image data of a plurality of frames in which the positional deviation is corrected, An ultrasonic image processing program characterized by realizing an image generation function for generating a three-dimensional image.

  As described above, according to the present invention, in the case where a plurality of two-dimensional ultrasonic images are acquired while rotating the ultrasonic scanning surface around a certain axis, and a three-dimensional image is reconstructed using these two images, respiratory movement is not affected. It is possible to realize an ultrasonic diagnostic apparatus, an ultrasonic image processing apparatus, and an ultrasonic image processing program that can remove noise caused by the noise.

  Hereinafter, first to third embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

(First embodiment)
FIG. 1 is a block diagram showing the configuration of the ultrasonic diagnostic apparatus according to the first embodiment. As shown in the figure, the ultrasonic diagnostic apparatus 1 includes an ultrasonic probe 12, an input device 13, a monitor 14, an ultrasonic transmission unit 21, an ultrasonic reception unit 22, a B-mode processing unit 23, a Doppler processing unit 24, An image generation unit 25, an image memory 26, an image composition unit 27, a control processor (CPU) 28, an internal storage unit 29, and an interface unit 30 are provided. Hereinafter, the function of each component will be described. The ultrasound diagnostic apparatus 1 is connected with an ECG unit for measuring an ECG signal (electrocardiogram signal) of the subject.

  The ultrasonic probe 12 generates ultrasonic waves based on a drive signal from the ultrasonic transmission / reception unit 21, converts a reflected wave from the subject into an electric signal, and a matching layer provided in the piezoelectric vibrator. And a backing material for preventing the propagation of ultrasonic waves from the piezoelectric vibrator to the rear. When ultrasonic waves are transmitted from the ultrasonic probe 12 to the subject P, the transmitted ultrasonic waves are successively reflected by the discontinuous surface of the acoustic impedance of the body tissue and received by the ultrasonic probe 12 as an echo signal. . The amplitude of this echo signal depends on the difference in acoustic impedance at the discontinuous surface that is supposed to be reflected. In addition, the echo when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component in the ultrasonic transmission direction of the moving body due to the Doppler effect, and the frequency Receive a shift.

  Note that the ultrasonic probe 12 included in the ultrasonic apparatus is capable of rotating the scanning plane around a predetermined axis. As a typical example, a two-dimensional array probe or an MTEE probe that can ultrasonically scan a three-dimensional region by electrical control using two-dimensionally arranged two-dimensional vibrating elements can be adopted. Here, the MTEE probe (multi-plane transesophageal ultrasound endoscope probe) can observe a cross section at an arbitrary angle by rotating a one-dimensional array transducer as shown in FIG. It is used when a probe is inserted into the esophagus and the heart is observed.

  The input device 13 is connected to the device main body 11, and various switches, buttons, and tracks for incorporating various instructions, conditions, region of interest (ROI) setting instructions, various image quality condition setting instructions, etc. from the operator into the device main body 11. It has a ball, mouse, keyboard, etc. For example, when the operator operates the end button or the FREEZE button of the input device 13, the transmission / reception of the ultrasonic wave is ended, and the ultrasonic diagnostic apparatus is temporarily stopped.

  Based on the video signal from the scan converter 25, the monitor 14 uses in-vivo morphological information (B-mode image), blood flow information (average velocity image, dispersion image, power image, etc.), and a combination thereof as an image. indicate.

  The ultrasonic transmission unit 21 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like (not shown). In the pulsar circuit, a rate pulse for forming a transmission ultrasonic wave is repeatedly generated at a predetermined rate frequency fr Hz (period: 1 / fr second). Further, in the delay circuit, a delay time necessary for focusing the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each rate pulse. The trigger generation circuit applies a drive pulse to the probe 12 at a timing based on this rate pulse.

  The ultrasonic transmission unit 21 has a function capable of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a predetermined scan sequence in accordance with an instruction from the control processor 28. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching the value or a mechanism for electrically switching a plurality of power supply units.

  The ultrasonic receiving unit 22 has an amplifier circuit, an A / D converter, an adder and the like not shown. The amplifier circuit amplifies the echo signal captured via the probe 12 for each channel. In the A / D converter, a delay time necessary for determining the reception directivity is given to the amplified echo signal, and thereafter, an addition process is performed in the adder. By this addition, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The B-mode processing unit 23 receives the echo signal from the transmission / reception unit 21, performs logarithmic amplification, envelope detection processing, and the like, and generates data in which the signal intensity is expressed by brightness. This data is transmitted to the scan converter 25 and is displayed on the monitor 14 as a B-mode image in which the intensity of the reflected wave is represented by luminance.

  The Doppler processing unit 24 performs frequency analysis on velocity information from the echo signal received from the transmission / reception unit 21, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and obtains blood flow information such as average velocity, dispersion, and power. Ask for multiple points.

  In general, the image generation unit 25 converts (scan converts) a scanning line signal sequence of an ultrasonic scan into a scanning line signal sequence of a general video format typified by a television or the like, and performs superconversion as a display image. A sonic diagnostic image is generated. Further, the image generation unit 25 executes a process (a process for removing noise caused by body movement) according to a function for removing noise caused by body movement, which will be described later. Note that data before entering the image generation unit 25 may be referred to as “raw data”. The volume rendering processor may have any configuration such as a CPU, GPU, DSP, ASIC, or the like.

  The image memory (cine memory) 26 is, for example, a memory that stores ultrasonic images corresponding to a plurality of frames immediately before freezing. By continuously displaying the images stored in the image memory 26 (cine display), an ultrasonic moving image can be displayed.

  The image synthesizing unit 27 synthesizes the image received from the image generating unit 25 or the character information and scales of various parameters, and outputs it as a video signal to the monitor 14.

  The control processor 28 has a function as an information processing apparatus (computer) and controls the operation of the main body of the ultrasonic diagnostic apparatus. The control processor 28 reads out a dedicated program for realizing a function of removing noise caused by body movement from the internal storage unit 29, a control program for executing predetermined image generation / display, and the like on its own memory. Expand and execute operations and controls related to various processes. The ECG signal from the ECG unit 2 is input to the control processor 28 via the interface unit 30. Based on the input ECG signal, the control processor 28 determines which cardiac time phase each frame obtained by the ultrasonic scan corresponds to.

  The internal storage unit 29 includes a predetermined scan sequence, a dedicated program for realizing a function of removing noise caused by body movement according to each embodiment, a control program for executing image generation and display processing, and diagnostic information (patient ID, doctor's findings, etc.), diagnostic protocol, transmission / reception conditions, CFAR processing control program, body mark generation program, and other data groups are stored. Further, it is also used for storing images in the image memory 26 as necessary. Data in the internal storage unit 29 can be transferred to an external peripheral device via the interface circuit 30.

  The interface unit 30 is an interface related to the input device 13, a network, and a new external storage device (not shown). Data such as ultrasonic images and analysis results obtained by the apparatus can be transferred to another apparatus via the network by the interface unit 30.

(Removal function for noise caused by body movement)
Next, a function for removing noise caused by body movements of the ultrasonic diagnostic apparatus 1 will be described. This function removes noise and distortion caused by body movements typified by breathing when scanning a 3D area while rotating the ultrasound scanning surface around a predetermined axis, and provides high-quality ultrasound images. Is to provide. In the present embodiment, for the sake of concrete explanation, a case where a diagnosis target is a heart and a three-dimensional region is scanned while rotating an ultrasonic scanning surface using an MTEE probe is taken as an example. However, the technical idea of the present invention is not limited to the example of the heart, and can be applied even when the diagnosis target is an abdominal region such as the liver. In this proposal, some fluctuations in the heartbeat period are allowed, but cases where the heartbeat period fluctuates greatly such as arrhythmia are excluded.

  FIG. 3 is a flowchart showing the flow of each process executed in the process according to the function for removing the noise caused by the body movement (the process for removing the noise caused by the body movement). Hereinafter, the contents of processing in each step will be described.

[Execution of 3D scan by MTEE, generation of 2D image: steps S1, S2]
First, using the ECG signal as a trigger, under the control of the control processor 28, a plurality of ultrasonic transducers of the ultrasonic probe 12 (MTEE probe) are rotated around the rotation axis for each scan (the rotation angle is changed). A three-dimensional scan is executed over a range of 180 °, and echo signals for a plurality of frames over a plurality of heartbeats (here, for example, echo signals for 16 frames as shown in FIG. 4) are obtained ( Step S1). In this scan, the signal changes temporally and spatially for each frame. Information (cardiac phase information) indicating which cardiac phase corresponds to each frame is acquired by the control processor 28 based on the ECG signal, and is automatically stored in the internal storage device 29, for example.

  The echo signals for a plurality of frames obtained by the scan are sent out to the B-mode processing unit 23 via the ultrasonic receiving unit 22 for each frame. The B mode processing unit 23 generates B mode image data for each frame.

  Next, the image generation unit 25 generates a two-dimensional image for each frame based on the B-mode image data for each frame (step S2).

[Extract each two-dimensional image of the same cardiac time phase: Step S3]
Next, the image generation unit 25 extracts each two-dimensional image of the same cardiac phase (cardiac cycle) using the cardiac phase information, and the position is spatially different (spatial) in each cardiac phase. A plurality of two-dimensional images are acquired (step S3).

  FIG. 5 is a diagram for explaining the processing in step S3. That is, among the 16 cross-sectional two-dimensional images acquired as shown in FIG. 4, FIG. 5A shows the first two-dimensional images 1, 5, 9, and 13 corresponding to the R-wave detection. Extracted, FIG. 5 (b) shows the extracted two-dimensional images 2, 6, 10, and 14 of the second cardiac time phases corresponding to R wave detection, FIG. 5 (c) corresponds to R wave detection FIG. 5 (d) shows the second two-dimensional images 4 and 8 between the fourth cardiac time phases corresponding to the R wave detection. , 12 and 15 are shown respectively.

[Calculation of motion vector: Step S4]
Next, the image generation unit 25 calculates a motion vector for each frame (for each scanning plane) (step S4). The motion vector calculation method is as follows.

  6 and 7 are diagrams for explaining the concept of the motion vector calculation method. As shown in FIGS. 6A and 6B, the central axis of the data of each frame in the same cardiac phase volume passes through the same line. Therefore, if there is no movement such as breathing, the data on the central axis of each frame should take the same value. As shown in FIG. 7, when images of lines on the center axis of each actual frame are arranged (the horizontal axis is frame No (rotation direction = Z direction), the vertical axis is distance direction (X direction)), about 4 You can see how the image changes by breathing every second.

  In order to correct this movement, the image generation unit 25 determines a reference frame k (for example, No. 1 frame), and the center axis of the k th frame and the n th frame (for example No. 5, 9,. The cross-correlation coefficients are calculated by shifting from the central axis of 13 frames) in the X direction, Y direction, and Z direction, and the maximum position (Δx, Δy, Δz) is set as a motion vector. At this time, as shown in FIG. 8, it is preferable to divide the line in the X direction and perform this processing for each block (however, FIG. 8 shows the ninth time phase as an example). Further, it is desirable to select a frame with no motion fluctuation as the reference frame k. Furthermore, instead of the cross-correlation coefficient, a position where the sum of absolute values of differences or the sum of squares of differences is minimized may be used.

[Motion correction processing: Step S5]
Next, in each frame, the image generation unit 25 calculates a motion vector for the entire frame from the motion vector for each block, and uses this to perform motion correction for each frame (step S5).

It can be seen from the motion vector of each block where the center position of the block is displaced. From this, for each frame, the image generation unit 25 determines the position of the observed tomographic plane from the many motion vectors corresponding to each block if there is no movement (more precisely, the state of the reference frame). Calculate what happened. That is, for each frame, the image generation unit 25 uses the motion vector corresponding to each block from the motion vectors corresponding to the x, y, and z axes shown in the following equation (1) and the rotation angle parameters ( 6) in total.

  Next, the image generation unit 25 moves the position of each point on the tomographic plane observed as shown in FIG. 9 using the equation (1) in which the parameter is determined for each frame. The observed tomographic plane as shown in (a) is arranged at a position (state corresponding to the reference frame) presumed to exist when there is no body movement as shown in FIG. 10 (b). As described above, the motion correction process is executed.

  In the present embodiment, there is no deformation, and the movement is limited to translation and rotation. Further, in order to calculate the parameter of the above formula (1), it is sufficient if there are at least two motion vectors. However, in this embodiment, in order to increase accuracy, parameters are estimated from a large number of motion vectors by the least square method.

[Three-dimensional image generation: Step S6]
The image generation unit 25 executes volume rendering based on the new cross-sectional position obtained by the motion correction process in step S5, and generates a three-dimensional image (step S6). The three-dimensional coordinate transformation at this time is complicated because the cross sections are no longer regularly arranged. However, as shown in FIG. 11 (a), the space position before coordinate conversion constituted by two adjacent frames and the position in the three-dimensional space as shown in FIG. 11 (b) are divided into a large number of polygons and defined. Is possible.

[Image display: Step S7]
The image synthesizing unit 27 synthesizes the image received from the image generating unit 25 or the character information and scales of various parameters. Next, the control unit 28 controls the display unit 14 so that the three-dimensional image combined with the character information or the like is displayed in a predetermined form.

(effect)
According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, when a three-dimensional region is scanned while rotating a scanning plane around a predetermined axis (rotating axis), a motion scanning plane (super The motion vector of the acoustic tomography is calculated, and the positional deviation between the scanning planes is corrected using this. Therefore, even when body movement due to breathing or the like occurs during an ultrasound scan, the influence of the body movement on the image can be removed, and a high-quality image without distortion can be provided. it can. As a result, when displaying a four-dimensional image of the heart or the like, it is possible to provide a reliable image at a relatively low cost without imposing a burden on the patient or the operator.

(Second Embodiment)
Next, a second embodiment of the present invention will be described. In order to increase the resolution in the rotation direction (Z direction), the ultrasound diagnostic apparatus 1 according to the present embodiment is close in time in addition to the frame corresponding to the cross-section of the same heart homology during motion correction. However, a frame corresponding to a cross section that is close in space (that is, close to the cardiac phase) and spatially close is also used.

  Next, a process for removing noise caused by body movement according to the present embodiment will be described.

  FIG. 12 is a flowchart showing a flow of a process for removing noise caused by body movement according to the present embodiment. When FIG. 3 is compared with FIG. 3, only step S4 'is different, and the contents of the other steps are substantially the same. Only different contents will be described below.

[Calculation of motion vector: Step S4 ′]
The image generation unit 25 calculates a motion vector for each frame using the same heart time homologous frame and the adjacent heart time phase frame (step S4 ′).

  That is, in FIG. 13, for example, when performing motion correction of the cross-section 5 of the first cardiac phase (consisting of the cross-sections of No. 1, 5, 9, and 13; see FIG. 5), the same cardiac homology is performed. No. In addition to the frames 1, 5, 9 and 13, the motion vector for the cross section 5 is also calculated using at least one cross section (for example, No. 4, 6, etc.) which are in different cardiac phases but are close to each other. . A specific calculation method is the same as that in the first embodiment.

  According to the configuration described above, when calculating the motion vector, in addition to the frame having the same cardiac phase as the frame to be corrected, it has a cardiac phase close to the frame to be corrected. A motion vector is calculated by using at least one frame that is spatially close, and the positional deviation of the cross section is corrected. Therefore, the resolution in the rotation direction can be improved, and more effective motion correction can be realized.

(Third embodiment)
Next, a second embodiment of the present invention will be described. The ultrasonic diagnostic apparatus 1 according to the present embodiment is, for example, a diagnostic target that is a part that does not periodically move, such as a liver, and does not require an ECG signal.

  FIG. 14 is a diagram for explaining a process for removing noise caused by body movement according to the present embodiment. In the example of this embodiment, the diagnostic object itself does not exercise. Therefore, as shown in FIG. 14, the data on the rotation axis of all the cross sections (that is, the cross sections of Nos. 1 to 16) should match if there is no body movement due to breathing or the like. For this reason, the ultrasonic diagnostic apparatus 1 uses data on the rotation axis of the entire cross section when calculating the motion vector in each frame.

  According to such a configuration, the resolution in the rotation direction can be further improved, and more effective motion correction can be realized.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the constituent elements without departing from the scope of the invention in the implementation stage. Specific examples of modifications are as follows.

  (1) Each function according to the present embodiment can also be realized by installing a program for executing the processing in a computer such as a workstation and developing the program on a memory. At this time, a program capable of causing the computer to execute the technique is stored in a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

  (2) In each of the above-described embodiments, the movement is defined as a uniform parallel movement amount and rotation angle of the cross section. However, the cross section may be divided into blocks, and the parallel movement and rotation may be performed for each block. . Further, it is possible to consider even distortion.

  (3) In each of the above embodiments, the B-mode image data as raw data is subjected to two-dimensional coordinate conversion, and then motion vector calculation and motion correction processing are executed to perform three-dimensional coordinate conversion (three-dimensional image generation). . On the other hand, without performing two-dimensional coordinate conversion, the above-described motion vector calculation and motion correction processing may be executed with the B-mode image data as raw data to perform three-dimensional coordinate conversion. .

  In addition, various inventions can be formed by appropriately combining a plurality of components disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, in the case where a plurality of two-dimensional ultrasonic images are acquired while rotating the ultrasonic scanning surface around a certain axis, and a three-dimensional image is reconstructed using these two images, respiratory movement is not affected. It is possible to realize an ultrasonic diagnostic apparatus, an ultrasonic image processing apparatus, and an ultrasonic image processing program that can remove noise caused by the noise.

FIG. 1 is a block diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to an embodiment. FIG. 2 is a diagram for explaining the configuration of the ultrasonic probe 12. FIG. 3 is a flowchart showing the flow of each process executed in the process of removing noise caused by body movement. FIG. 4 is a diagram for explaining the contents of a three-dimensional scan by MTEE. FIG. 5 is a diagram for explaining processing for extracting two-dimensional images of the same cardiac phase. 6A and 6B are diagrams for explaining the concept of a motion vector calculation method. FIG. 7 is a diagram for explaining the concept of a motion vector calculation method. FIG. 8 is a diagram for explaining the concept of a motion vector calculation method. FIG. 9 is a diagram for explaining a process of correcting the movement of the scanning plane caused by body movement. FIGS. 10A and 10B are diagrams for explaining processing for correcting the movement of the scanning plane caused by body movement. FIG. 11 is a diagram for explaining a process of generating a three-dimensional image. FIG. 12 is a flowchart showing a flow of a process for removing noise caused by body movement according to the second embodiment. FIG. 13 is a diagram for explaining motion vector calculation processing according to the second embodiment. FIG. 14 is a diagram for explaining a process for removing noise caused by body movement according to the third embodiment. FIG. 15 is a diagram for explaining the prior art.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Ultrasonic diagnostic apparatus, 2 ... ECG unit, 12 ... Ultrasonic probe, 13 ... Input device, 14 ... Monitor, 21 ... Ultrasonic transmission unit, 22 ... Ultrasonic reception unit, 23 ... B mode processing unit, 24 ... Doppler processing unit, 25 ... scan converter, 26 ... cine memory, 27 ... image compositing unit, 28 ... control processor, 29 ... internal storage unit, 30 ... interface unit

Claims (9)

An ultrasonic image data acquisition unit that three-dimensionally scans the diagnostic object while rotating the scanning surface about the rotation axis, and acquires ultrasonic image data of a plurality of frames corresponding to the plurality of scanning surfaces;
Correction means for correcting a positional deviation between the frames based on data corresponding to the rotation axis of the plurality of ultrasonic image data;
Image generation means for generating a three-dimensional image using ultrasonic image data of a plurality of frames in which the positional deviation is corrected,
An ultrasonic diagnostic apparatus comprising: The diagnostic object is a heart,
The correction means includes
Based on the data corresponding to the rotation axis of the ultrasonic image data of the same heart homology with the frame to be corrected among the plurality of ultrasonic image data, the motion vector of each frame is calculated,
Using the motion vector to correct misalignment between the frames;
The ultrasonic diagnostic apparatus according to claim 1. The diagnostic object is a heart,
The correction means includes
Among the plurality of ultrasonic image data, data corresponding to the rotation axis of ultrasonic image data having the same heart homology with the frame to be corrected, and the frame to be corrected and temporally and spatially Calculating a motion vector of each frame based on the data corresponding to the rotation axis of the ultrasound image data corresponding to at least one adjacent frame;
Using the motion vector to correct misalignment between the frames;
The ultrasonic diagnostic apparatus according to claim 1. The diagnostic object is an organ other than the heart,
The correction means calculates the motion vector using data corresponding to the rotation axis of the frame to be corrected and data corresponding to the rotation axis of each frame other than the frame to be corrected. And
Using the motion vector to correct misalignment between the frames;
The ultrasonic diagnostic apparatus according to claim 1. The correction means includes
Dividing each ultrasonic image data into a plurality of blocks;
Calculate with the motion vector for each block of each frame,
Calculating the motion vector for each frame using the motion vector for each block, and using this to correct misalignment between the frames;
The ultrasonic diagnostic apparatus according to any one of claims 2 to 4, wherein: The correction means includes
Dividing each ultrasonic image data into a plurality of blocks, calculating the motion vector for each block of each frame;
Correcting the positional deviation between the frames by correcting the positional deviation for each block of the frame using the motion vector for each block;
The ultrasonic diagnostic apparatus according to any one of claims 2 to 4, wherein:   The ultrasonic diagnostic apparatus according to claim 1, wherein the correction unit calculates the motion vector after two-dimensional coordinate conversion of the plurality of ultrasonic image data. Storage means for storing ultrasonic image data of a plurality of frames corresponding to a plurality of scanning planes acquired by three-dimensionally ultrasonically scanning a diagnosis target while rotating the scanning plane about a rotation axis;
Correction means for correcting a positional deviation between the frames based on data corresponding to the rotation axis of the plurality of ultrasonic image data;
An ultrasonic diagnostic image processing apparatus comprising: On the computer,
Among the plurality of frames of ultrasonic image data corresponding to a plurality of scanning planes acquired by three-dimensionally ultrasonically scanning the diagnosis target while rotating the scanning plane about the rotation axis, A correction function for correcting the positional deviation between the frames based on the corresponding data;
An image generation function for generating a three-dimensional image using ultrasonic image data of a plurality of frames in which the positional deviation is corrected;
An ultrasonic image processing program characterized by realizing the above.

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